Managing preload reserve by tracking the ventricular operating point with heart sounds

ABSTRACT

A system and method for managing preload reserve and tracking the inotropic state of a patient&#39;s heart. The S1 heart sound is measured as a proxy for direct measurement of stroke volume. The S3 heart sound may be measured as a proxy for direct measurement of preload level. The S1-S3 pair yield a point on a Frank Starling type of curve, and reveal information regarding the patient&#39;s ventricular operating point and inotropic state. As an alternative, or in addition to, measurement of the S3 heart sound, the S4 heart sound may be measured or a direct pressure measurement may be made for the sake of determining the patient&#39;s preload level. The aforementioned measurements may be made by a cardiac rhythm management device, such as a pacemaker or implantable defibrillator.

CROSS REFERENCE TO RELATED APPLICATION

This application is a divisional of U.S. application Ser. No.11/189,462, filed Jul. 26, 2005, which is hereby incorporated byreference in its entirety.

TECHNICAL FIELD

The present document relates to cardiac rhythm management devicesgenerally, and more particularly to cardiac rhythm management devicesthat monitor the inotropic state exhibited by a heart, detect changes inthe inotropic state, and identify the particular operating pointexhibited by a heart.

BACKGROUND

Heart failure is a condition wherein the heart fails to circulate bloodsufficiently to meet the metabolic demands of the various tissues of thebody. In other words, cardiac output is insufficient to satisfy thebody.

Cardiac output is influenced by the stroke volume exhibited by theheart. For a given heart, stroke volume may be considered a function ofpreload and inotropic state. Briefly, preload refers to the stretchingof the myocardial cells in a chamber (e.g., left ventricle) duringdiastole, before contraction of the chamber. Preload may be measured asthe end-diastolic volume or pressure exhibited by the blood within thechamber in question. Inotropic state refers generally to the hormonalmilieu exerting influence upon the heart. The inotropic state of a heartdetermines the strength of its next contraction.

A Frank Starling curve presents the relationship between stroke volume,preload, and inotropic state for a given heart. An exemplary FrankStarling curve is depicted in FIG. 1. The chart of FIG. 1 is plotted ona Cartesian plane, with stroke volume measured along the y-axis, andpreload measured along the x-axis. Three solid curves 100, 102, and 104are depicted on the chart. Each curve 100, 102, and 104 corresponds to adifferent inotropic state. Curve 100 corresponds to inotropic state S₁,curve 102 corresponds to inotropic state S₂, and curve 104 correspondsto inotropic state S₃.

The inotropic state exhibited by a person's heart may vary with exertionor emotional state, among other factors. Thus, for example, inotropicstate S1 (curve 100) may represent the inotropic state of a particularperson's heart during ordinary waking non-strenuous activity. State S2(curve 102) may represent the inotropic state of the person's heartduring strenuous exertion, and state S3 (curve 104) may represent theinotropic state of the person's heart during rest. As can be seen fromFIG. 1, when the inotropic state exhibited by a heart elevates, agreater stroke volume is yielded for a given level of preload (becausethe hormonal influences upon the heart cause the heart to contract moreforcefully). Conversely, when the inotropic state exhibited by a heartdepresses, a lesser stroke volume is yielded for a given level ofpreload.

SUMMARY

As can be seen in FIG. 1, the stroke volume-preload curve for a giveninotropic state is generally a monotonic, increasing curve. Therefore,stroke volume may be elevated by elevating a patient's preload. However,as can also be seen from FIG. 1, the stroke volume-preload curve for aninotropic state tends to level off (exhibit only a slight positivederivative) after a particular level of preload, referred to as the“critical preload.”

For a given inotropic state, elevating a patient's preload beyond thecritical preload is generally not an effective strategy for increasingstroke volume, and may lead to pulmonary congestion. Briefly, anelevation in preload corresponds to an elevation in end-diastolicpressure exhibited by the blood in, for example, the left ventricle.Elevated pressure in the left ventricle leads to elevated pressure inthe left atrium, which, in turn, leads to elevated pressure in the veinsof the lungs. If the pressure in the veins of the lungs exceeds a givenpoint, plasma leaves the circulation space of the lungs and enters intothe intercellular space therein. This condition, referred to as“pulmonary congestion,” interferes with the oxygen exchange function ofthe lungs, and leaves the patient short of breath.

A patient with heart failure generally exhibits a stroke volume-preloadcurve that is depressed. An exemplary curve 106 typical of heart failureis shown in FIG. 1. The curve 106 reveals that the patient's heartproduces little stroke volume. One strategy for dealing with such apatient is to elevate the patient's preload (e.g., administerintravenous fluids or administer salt), so that the patient's strokevolume will rise. However, as discussed above, such a strategy shouldnot be pursued to the point of elevating the preload beyond the criticalpreload. To achieve gains in stroke volume beyond what may be achievedby elevation of preload, the patient's inotropic state may be elevated(e.g., by administration of an inotrope, for example). By practicing atwo-pronged approach of elevating both preload and inotropic state, aheart failure patient may attain a satisfactory stroke volume, whilereducing the risk of pulmonary congestion.

The foregoing discussion reveals the desirability of a device and/orsystem for monitoring a patient's preload, stroke volume, and inotropicstate. It is particularly desirable to achieve such an end with the useof existing technology, thereby requiring minimal risk and investment.Against this backdrop, the present invention was developed. According toone embodiment of the present invention, a method includes monitoring anS1 heart sound emitted by a heart of a patient. The method also includesmonitoring a proxy variable indicating preload exhibited by the heart.Finally, it is determined whether the heart has exhibited an inotropicstate change, using at least the S1 heart sound and the proxy variable.

According to another embodiment of the present invention, a methodincludes sensing a plurality of S3 or S4 heart sounds emitted by a heartof a patient, each of which is represented as a time-varying signal withat least one maxima and minima. The method also includes finding agreatest difference between a minima and maxima that are consecutive foreach of the time-varying signals representing the plurality of S3 or S4heart sounds, thereby yielding a set of peak-to-peak differences.Finally, the inotropic state of the heart is monitored, using the set ofpeak-to-peak differences and an indicator of stroke volume.

According to yet another embodiment of the present invention, a systemincludes a preload altering device, and an implantable device. Theimplantable device includes a transducer. The implantable device alsoincludes a control circuit coupled to the transducer. The controlcircuit is configured to cooperate with the transducer to monitor an S1heart sound emitted by a heart of a patient, monitor a proxy variableindicating preload exhibited by the heart, and communicate a controlsignal to the preload altering device.

According to yet another embodiment of the present invention, a systemincludes an inotropic state altering device and an implantable device.The implantable device includes a transducer and a control circuitcoupled to the transducer. The control circuit is configured tocooperate with the transducer to monitor an S1 heart sound emitted by aheart of a patient, monitor a proxy variable indicating preloadexhibited by the heart, and communicate a control signal to theinotropic state altering device using the inotropic state.

According to yet another embodiment of the present invention, a deviceincludes a transducer and a control circuit coupled to the transducer.The control circuit is configured to cooperate with the transducer tomonitor an S1 heart sound emitted by a heart of a patient, and monitor aproxy variable indicating preload exhibited by the heart.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 depicts an exemplary Frank Starling curve.

FIG. 2A depicts a scatter graph that relates left ventricularend-diastolic pressure (LVEDP) to the maximum peak-to-peak amplitudeexhibited by the third heart sound.

FIG. 2B depicts an exemplary isolated S3 heart sound 200, as observedvia an accelerometer located within a pacemaker implanted in a patient.

FIG. 3 depicts a method by which a point on a Frank Starling type ofcurve may be determined, according to an embodiment of the presentinvention.

FIG. 4 depicts a Frank Starling type of curve, according to an aspect ofthe present invention.

FIG. 5 depicts an exemplary method for controlling the alteration of apatient's inotropic state, according to an embodiment of the presentinvention.

FIG. 6 depicts an exemplary method for determining whether a patientpreload exceeds the critical preload, according to an embodiment of thepresent invention.

FIG. 7 depicts a method for determining whether a particular cardiaccondition is indicated, according to an embodiment of the presentinvention.

FIG. 8 depicts an exemplary system useful for detecting heart sounds,and executing any of the schemes and methods disclosed herein.

DETAILED DESCRIPTION

By way of brief background, the heart circulates blood through a knownsequence of cardiac chamber contractions, relaxations, and valvemanipulations. The heart makes certain sounds as it progresses through acardiac cycle, which are caused by the circulation of the blood and theopening and closing of various heart valves. These heart sounds occur ina characteristic sequence in a cardiac cycle, and are respectivelyreferred to as S1, S2, S3 and S4.

The S1 heart sound is caused by acceleration and deceleration of blood,and closure of the mitral and tricuspid valves. The S1 heart soundgenerated during a given cardiac cycle exhibits morphologicalcharacteristics (e.g., median peak-to-peak amplitude of a set of S1heart sounds) are indicative of the maximum rate of change of pressurein the left ventricle during the given cardiac cycle. S2 is believed tobe indicative of, among other things, aortic valve closure and pulmonaryvalve closure. S3 is known to be a ventricular diastolic filling soundoften indicative of certain pathological conditions including heartfailure. S4 is believed to be a ventricular diastolic filling soundresulted from atrial contraction and is usually indicative ofpathological conditions.

FIG. 2A depicts a scatter graph that relates left ventricularend-diastolic pressure (LVEDP) to the maximum peak-to-peak amplitudeexhibited by the third heart sound (referred to as “S3”). The chart ofFIG. 2A is a Cartesian plane, with left ventricular end-diastolicpressure measured along the y-axis, and maximum peak-to-peak S3amplitude measured along the x-axis.

Each point on the Cartesian plane represents data taken from anindividual patient. For each patient, a pressure sensor was introducedinto the patient's left ventricle, thereby enabling direct measurementof left ventricular end-diastolic pressure. Additionally, a pacemakerhaving an internal accelerometer was placed upon each patient's chest.(As used herein, the term “pacemaker” refers generally to anyimplantable cardiac rhythm management device, and includes within itsmeaning cardiac pacemakers, implantable defibrillators, cardiacresynchronization therapy (CRT) devices, implantable defibrillatorshaving pacing and/or CRT capabilities, and pacemakers having CRTcapabilities). For each of a set of N heartbeats, the patient's leftventricular end-diastolic pressure was directly measured, and themaximum peak-to-peak S3 amplitude observed by the accelerometer in thepacemaker was recorded. After obtaining the data for a given patient,the pressure measurements were averaged, resulting in an average leftventricular end-diastolic pressure exhibited by a given patient. Also,for a given patient, the median value of the N maximum peak-to-peak S3measurements was found, yielding a median maximum peak-to-peak S3amplitude exhibited by a given patient. The Cartesian plane of FIG. 2was constructed by plotting the average left ventricular end-diastolicpressure exhibited by a given patient against the median maximumpeak-to-peak S3 amplitude exhibited by a given patient.

As can be seen from FIG. 2A, a generally linear relationship existsbetween left ventricular end-diastolic pressure and maximum peak-to-peakS3 amplitude. Therefore, maximum peak-to-peak S3 amplitude (or a medianof multiple such measurements) may be used as a proxy for directmeasurement of left ventricular end-diastolic pressure (i.e., preload).

FIG. 2B presents an exemplary isolated S3 heart sound 200, as observedvia an accelerometer located within a pacemaker implanted in a patient.The S3 heart sound 200 of FIG. 2 includes seven peaks. To find themaximum peak-to-peak value exhibited by the S3 heart sound, one may usevarious alternatives. For example, one may find the difference betweenthe greatest positive-going peak (identified by the label “Max”) and thegreatest negative-going peak (identified by the label “Peak₂”). Thus,the difference in amplitude between Max and Peak₂ may represent themaximum peak-to-peak value of the S3 heart sound. Thereafter, the medianof a populace of such amplitudes is found, in order to arrive at amedian peak-to-peak amplitude. Alternatively, one may find the greatestdifference in consecutive peaks. Thus, for example, the differencebetween Peak₁ and Peak₂ may represent the maximum peak-to-peak value ofthe S3 heart sound 200. Again, the median or other central tendency of apopulace of such amplitudes may be found, in order to arrive at a medianor like peak-to-peak amplitude.

The inventors have discovered, among other things, that calculating themaximum peak-to-peak value of an S3 heart sound according to the lattermethod results in better correlation to left ventricular end-diastolicpressure. Nevertheless, both alternatives and the like are within thescope of the present invention.

In addition to the methods of finding a median peak-to-peak amplitude ofan S3 (or other) heart sound just as described, the following method mayalso be employed. One may first find the median maximum peak exhibitedby a populace of S3 (or S1 or other) heart sounds, and may also find themedian minimum peak exhibited by the same populace of S3 (or S1 orother) heart sounds. Then, the difference between the two medians may befound, thereby arriving at the median peak-to-peak amplitude for apopulace of heart sounds.

The S1 heart sound relates to contractility, which, in turn, relates tostroke volume. For example, the median peak-to-peak amplitude of an S1heart sound relates to contractility. The median peak-to-peak amplitudeof a set of S1 heart sounds may be found according to the aforementionedmethods.

Because the S3 heart sound may be measured as a proxy for directmeasurement of preload, and because the S1 heart sound may be measuredas a proxy for measurement of stroke volume, a point on a Frank Starlingtype of curve may be determined indirectly via detection of heartsounds. Thus, for example, the point 108 on the Frank Starling curve ofFIG. 1 may be approximated by measurement of the S3 heart sound todetermine the point's 108 x-coordinate, and by measurement of the S1heart sound to determine the point's 108 y-coordinate.

FIG. 3 depicts a method by which a point on a Frank Starling type ofcurve may be determined. As discussed below, variations of the method ofFIG. 3 exist. The method of FIG. 3 begins by detecting the varioussounds (S1, S2, etc.) emitted during a cardiac cycle, as shown inoperation 300. Next, the heart sounds detected in operation 300 may beensemble averaged with the heart sounds detected over the last M cardiaccycles, as shown in operation 302. M may be an integer greater than orequal to one. If M is equal to one, then no ensemble averaging occurs,and a single heart sound is instead used to obtain the desiredinformation. The particular value assigned to M is a design choiceinfluenced by, amongst other factors, the noise content of the heartsound signal. After execution of operation 302, the S1 heart sound isisolated from the ensemble-averaged signal (operation 304). Also, the S3heart sound is isolated therefrom (operation 306).

The median peak-to-peak amplitudes of the last N ensemble-averaged S1and S3 heart sounds are then determined (operations 308 and 310,respectively). N may be any positive number greater than or equal toone. In one embodiment, N may be assigned a value equal to M (seeoperation 302). The median peak-to-peak amplitudes determined duringoperation 308 and 310 may be found according to any of the methodsdiscussed with reference to FIG. 2B.

The method of FIG. 3 may be used to find a point on a Frank Starlingtype of curve, as shown in FIG. 4. As can be seen from FIG. 4, themedian peak-to-peak amplitude exhibited by a set of N S3 sounds is usedto determine an x-coordinate of a point on a Frank Starling type ofcurve, and the median peak-to-peak amplitude exhibited by a set of N S1heart sounds is to determine a y-coordinate.

The method of FIG. 3 may be modified to make use of other proxies forpreload. For example, there exists a relationship between the S4 heartsound and the stiffness of the left ventricle during the active fillingperiod. Therefore, the method of FIG. 3 may be modified to take accountof the S4 heart sound, either as a replacement for, or in addition to,the S3 heart sound. For example, the span of time between the P wave andthe origination of the S4 heart sound reveals information about preload:the shorter the span of time, the greater the pressure. Thus, forexample, the method of FIG. 3 may be modified to find the median of thereciprocal of the span of time between the P wave and the origination ofthe S4 heart sound for a set of N cardiac cycles. The aforementionedmedian may be used to determine the x-coordinate of the point on theFrank Starling curve. In addition, the method of FIG. 3 may be modifiedto find the median peak-to-peak amplitude exhibited by the S4 heartsound, instead of (or in addition to) the median peak-to-peak amplitudeexhibited by the S3 heart sound. Still further, the method of FIG. 3 maybe modified to utilize a direct pressure measurement obtained by apressure sensor (such as may be introduced into the right ventricle orpulmonary artery, for example). Thus, a median value pressure exhibitedover a set of N cardiac cycles may be used to determine thex-coordinate.

The method of FIG. 3, or any of its aforementioned variations, may beused as a means by which to determine whether a patient's inotropicstate has changed. Such a determination may be useful, for example, indetermining an appropriate therapy such as the proper dosing of aninotrope or other substance for a given patient. An exemplary method isdepicted in FIG. 5.

The particular exemplary method depicted in FIG. 5 is useful, forexample, in a setting in which an inotrope or other substance is beingadministered to a patient, in an effort to elevate the patient'sinotropic state. Although the exemplary method of FIG. 5 determineswhether a patient's inotropic state has been sufficiently elevated, themethod of FIG. 5 may be altered to determine whether a patient'sinotropic state has been sufficiently depressed, should such adetermination be desired.

The method of FIG. 5 commences by determining a point on a FrankStarling type of curve, as shown in operation 500. Operation 500 may beeffectuated by execution of the method of FIG. 3 or any of itsvariations. After execution of operation 500, an x and y coordinatedescribing the patient's inotropic state is known.

Next, as shown in operation 502, a process known to alter a person'sinotropic state is commenced. For example, operation 502 may includeadministration of an inotrope to a patient, in order to elevate thepatient's inotropic state. An inotrope may be administered by anintravenous drip apparatus, for example, or by another substancedispenser, which serve as an inotropic state altering device when soused. After initiation of the process of operation 502, the patient's xand y coordinates on the Frank Starling type of curve is once againfound, as shown in operation 504. Thus, by virtue of execution ofoperations 500 and 504, a set of “before” and “after” points on a FrankStarling type of curve are determined for the patient.

In operation 506, two sets of coordinates for the patient are compared.In the context of an initial iteration through the process, thecomparison occurs between the coordinates determined in operation 500(i.e., the “before” coordinates) and the coordinates determined inoperation 504 (i.e., the “after” coordinates). In the context of asubsequent iteration, the comparison occurs between a set of coordinatesdetermined at one point in time and a most recent or other set ofcoordinates determined at an earlier point in time, with both points intime occurring after initiation of the process of operation 502. Turningto the comparison itself, if the comparison reveals that the xcoordinate has not increased, but that the y coordinate has increased,then it may be inferred that the patient's inotropic state has beenelevated.

If the patient's inotropic state has not been elevated, then control maybe passed to operation 508. Operation 508 is optional. In operation 508,one or more parameters controlling the process are altered. For example,if the process of operation 502 includes applying cardiacresynchronization therapy (CRT) to the patient, then one or moreparameters determining the CRT, such as the atrioventricular delay, maybe altered in order to improve the process' ability to elevate thepatient's inotropic state. Other examples of CRT control parametersinclude, without limitation, selecting which particular electrode(s) touse for delivering CRT electrical stimuli. If the nature of the processof operation 502 does not allow for alteration of a control parameter(e.g., administration or other delivery of an inotrope), operation 508may be omitted altogether, meaning that the process merely continues on,until an elevation in inotropic state is observed.

If, on the other hand, the patient's inotropic state has been elevated,control is passed to operation 510, in which it is determined whetherthe patient's stroke volume (inferred from the y-coordinate) has beensufficiently increased. If not, control is returned to optionaloperation 508. If operation 508 has been omitted, then control isreturned to operation 506. If it is determined that the patient'sinotropic state has been sufficiently elevated given the medical goalsassociated with the patient, then control is passed to operation 512. Inoperation 512, the process of operation 502 may be terminated, ifappropriate (e.g., administration of an inotrope), or the process may bepermitted to carry on, if appropriate (e.g., execution of CRT therapy).

Earlier, it was stated that the method of FIG. 5 may be altered todetermine whether a patient's inotropic state has been depressed. Suchan alteration includes changing the comparison of operation 506 toidentify an occurrence in which the x coordinate did not decrease, butthe y coordinate decreased. Such an occurrence indicates depression ofthe patient's inotropic state. The alteration may also include modifyingoperation 510 to determine whether the patient's stroke volume (inferredfrom the y-coordinate) has been sufficiently decreased, given themedical goals associated with the patient.

FIG. 6 depicts an exemplary method for determining whether a patientpreload exceeds the critical preload. The method of FIG. 6 may be usefulin a setting in which the patient's preload level is being adjusted. Forexample, a diuretic may be administered to a patient for the purpose oflowering the patient's preload level. A diuretic may be administered viaan intravenous drip apparatus or other form of substance dispenser, forexample, which serves as an example of a preload altering device when soused. The method of FIG. 6 may be used to determine that the patient'spreload level has been brought beneath the critical preload. The methodof FIG. 6 may be altered to detect a circumstance in which a patient'spreload level has been elevated beyond the critical preload.

The method of FIG. 6 commences by determining a point on a FrankStarling type of curve, as shown in operation 600. Operation 600 may beeffectuated by execution of the method of FIG. 3 or any of itsvariations. After execution of operation 600, an x and y coordinatedescribing the patient's inotropic state is known.

Next, as shown in operation 602, a process known to alter a person'spreload level is commenced. For example, operation 602 may includeadministration of a diuretic to a patient, in order to reduce thepatient's preload level. After initiation of the process of operation602, the patient's x and y coordinates on the Frank Starling type ofcurve is once again found, as shown in operation 604. Thus, by virtue ofexecution of operations 600 and 604, a set of “before” and “after”points on a Frank Starling type of curve are determined for the patient.

In operation 606, the slope between two sets of coordinates for thepatient is found. In the context of an initial iteration through theprocess, the slope is found between the coordinates determined inoperation 600 (i.e., the “before” coordinates) and the coordinatesdetermined in operation 604 (i.e., the “after” coordinates). In thecontext of a subsequent iteration, the slope is found between a set ofcoordinates determined at one point in time and a set of coordinatesdetermined at a most recent or other earlier point in time, with bothpoints in time occurring after initiation of the process of operation602.

After finding the slope in operation 606, the slope is compared to athreshold, as depicted in operation 608. The threshold is chosen to be avalue that approximately corresponds with the critical preload level ona Frank Starling curve. If the slope is less than the threshold, thenthe preload level is inferred to be beyond the critical preload level.In such a circumstance, control is returned to operation 602, meaningthat the process of operation 602 continues (e.g., administration of adiuretic), and that another set of coordinates for the patient will bemeasured.

On the other hand, if the slope is greater than the threshold, it may beinferred that the patient's preload level is less than the criticalpreload level, in which case control is passed to operation 610. Inoperation 610, the process of operation 602 may be terminated, ifappropriate. For example, if operation 602 included administration of adiuretic, then such administration may be halted by operation 610.

FIG. 7 depicts a method for determining whether a particular cardiaccondition (e.g., acute heart failure decompensation) is indicated. Themethod of FIG. 7 commences with measuring a point on a Frank Starlingtype of curve, as shown in operation 700. Operation 700 may use themethod of FIG. 3 or any of its variations. After operation 700, an x andy coordinate describing the patient's inotropic state is known. Afterexecution of operation 700, control is passed to operation 702.

Operation 702 is an optional operation, and may be omitted altogether.In operation 702, the x and y coordinate obtained in operation 700 arecombined with other information. The other information accessed inoperation 702 may include any information obtained by a pacemaker, suchas activity level information, respiration rate information, postureinformation, or past x and y coordinate information.

Based upon the combination of information (or based solely upon theinformation from operation 700), it is determined whether a particularcardiac condition is indicated in operation 704. For example, bycombining activity level and x and y coordinate information, it may bedetermined that a patient's heart exhibits an abnormally low strokevolume for a given preload and activity level. Accordingly, it may beinferred that the patient is exhibiting acute heart failuredecompensation. If no particular cardiac condition is detected inoperation 704, control returns to operation 700, and monitoring of thepatient's preload and stroke volume proxies continues. On the otherhand, if a particular cardiac condition is detected, control may pass tooperation 706.

Operation 706 is optional. In operation 706, occurrence of the detectedcondition is communicated. The communication may occur between animplanted cardiac management device (performing operations 700-706) anda programmer, a personal digital assistant, an access point to anetwork, such as a wireless or wired network, or to a wirelesscommunication device that may forward the message to an access point forcommunication to a remote computing system, for example. (The programmeror personal digital assistant may relay such a message to a remotecomputing system). Alternatively, the communication may occur betweenthe detection routine executing on the internal controller and a historylogging routine executed by the same internal controller. Thus, theoccurrence of the detected condition is logged, so that a health careprofessional may become aware of the condition, for example, the nexttime he or she reads the data contained in the log. After execution ofoperation 706, control is returned to operation 700, and monitoringcontinues.

The method of FIG. 7 may be performed continually or repeatedly. Forexample, a patient may be monitored for a given cardiac condition onceper day (e.g., at night) or several times each day, meaning that themethod of FIG. 7 would be executed once per day or several times perday.

FIG. 8 depicts an exemplary system useful for detecting heart sounds,and executing any of the schemes and methods disclosed herein.

In FIG. 8, an exemplary system 800 for detecting and processing heartsounds includes an implantable system 802 and an external system 804.The implantable system 802 and external system 804 are configured tocommunicate via a communications link 806.

The implantable system 802 includes an implantable device 808operatively coupled to a patient's heart by a lead system 812. Thecomponents of the implantable device 808 typically include an atrialsense amplifier 814, a ventricular sense amplifier 816, an atrialstimulating circuit 818, a ventricular stimulating circuit 820, acontroller 822, a memory 824, an accelerometer 826, an analogpre-processing circuit 828, an analog-to-digital (A/D) converter 830,and an input/output (I/O) interface 832. The components of implantabledevice 808 are typically housed within an implantable housing (indicatedby the broken lined box in FIG. 8), which may be implanted within thepatient's chest cavity (e.g., in the pectoral region) or elsewhere.

The atrial sense amplifier 814, ventricular sense amplifier 816, atrialstimulating circuit 818 and ventricular stimulating circuit 820 aretypically operatively coupled to the lead system 812 via a pair ofconductors 834. The lead system 812 may include an atrial sensingelectrode and an atrial stimulating electrode adapted to be disposed inthe right atrial chamber of heart and a ventricular sensing electrodeand a ventricular stimulating electrode adapted to be disposed in theright ventricular chamber of the heart.

Sensed atrial and ventricular electrical signals generated by thesensing electrodes are received by the atrial and ventricular senseamplifiers 814 and 816, respectively. Similarly, atrial and ventricularstimulating signals generated by the atrial and ventricular stimulatingcircuits 818 and 820 are applied to the atrial and ventricularstimulating electrodes, respectively. The atrial sense amplifier 814,ventricular sense amplifier 816, atrial stimulating circuit 818, andventricular stimulating circuit 820, are each also operatively coupledto the controller 822.

In other embodiments, other sensing electrode configurations are usedfor internally sensing one or more electrical signals of the heart. Inone example, only one sensing electrode may be used. Alternatively, oneor more electrodes placed within the body but outside of the heart areused for sensing cardiac electrical signals. In yet another example, asensing electrode is placed on the implantable housing. In each of theseexamples, the sensing electrodes are operatively coupled to thecontroller 822.

In the embodiment shown in FIG. 8, the sensing electrodes and thestimulating electrodes are disposed in association with the right sideof heart. In other embodiments, one or more sensing electrode(s) and oneor more stimulating electrode(s) are disposed in association with theleft side of the heart (in lieu of being disposed in association withthe right side of the heart, or in addition to sensing electrode(s) andstimulating electrode(s) disposed in association with the right side ofthe heart). The addition of left heart sensing may advantageously allowfor the resolution of ambiguities due to disassociation of right andleft heart conduction.

The controller 822 includes a microcontroller or microprocessor which isconfigured to execute a program stored in a read-only memory (ROM)portion of a memory unit 824, and to read and write data to and from arandom access memory (RAM) portion of the memory unit 824. By executingthe program stored in memory 824, the controller 822 is configured toprocess the atrial and ventricular electrical signals from the atrialand ventricular sense amplifiers 814 and 816, and to provide controlsignals to the atrial and ventricular stimulating circuits 818 and 820.In response, the stimulating circuits 818 and 820 provide stimulatingpulses to the heart via atrial and ventricular stimulating electrodes atappropriate times. In other embodiments, the controller 822 may includeother types of control logic elements or circuitry.

The implantable device 808 may be referred to as a dual-chamberpacemaker since pacemaking functions are provided to both atrial andventricular chambers of the heart. In another embodiment, theimplantable system includes a single-chamber pacemaker that senseselectrical signals and provides stimulating pulses to a single chamberof the heart. In yet another embodiment, the implantable system does notprovide any stimulation of heart tissues, but includes one or moresensing electrodes for sensing one or more electrical signals of theheart, and for providing corresponding sensed signals to controller 822.In still another embodiment, the implantable system does not provide anysensing electrodes for sensing any cardiac electrical signals, but isconfigured to sense signals representing heart sounds using a sensorsuch as the accelerometer 826, as described below, and to transmitinformation about such heart sounds from the implantable device 808.

In this description, the implantable device 808 is described as adual-chamber pacemaker for the sake of illustration. It is to beunderstood, however, that implantable system 802 need not provide thestimulation functions described herein, and may provide other functionswhich are not described herein.

In some embodiments, a minute ventilation output channel and a minuteventilation input channel may be included. The minute ventilation outputchannel generates a test signal that is applied to a portion of thepatient's thorax. An input channel receives and conditions a responsivesignal. The content of the conditioned signal reveals respirationinformation.

An accelerometer 826 may be configured to provide sensed signals to theanalog pre-processing circuit 828, which generates an analog outputsignal which is digitized by A/D converter 830. The digitizedaccelerometer signal is received by the controller 822. In theembodiment of FIG. 8, the accelerometer 826 is located within thehousing of implantable device 808. In another embodiment, theaccelerometer 826 is located on the housing of the implantable device.The accelerometer 826 may include, for example, a piezo-electric crystalaccelerometer sensor of the type used by pacemakers to sense the levelof physical activity of the patient, or may include other types ofaccelerometers. To detect heart sounds, this or other types ofsound-detecting sensors or microphones may also be used, such as apressure sensor or a vibration sensor configured to respond to soundsmade by the heart.

In another embodiment, the system 800 includes two or moresound-detecting sensors. In such an embodiment, the plurality of sensedheart sound signals from the plurality of sensors may be individuallytransmitted to external system 804 for display as individual traces, maybe combined (e.g., averaged) by external system 804 before beingdisplayed as a single trace, or may be combined by controller 822 beforebeing transmitted to external system 804 as a single heart sound signal.These sensors may include different types of sensors, sensors that arelocated in different locations, or sensors that generate sensed signalswhich receive different forms of signal processing.

In one embodiment, the accelerometer 826 is configured to generatesensed signals representative of two distinct physical parameters: (1)the level of activity of the patient; and (2) the heart sounds generatedby heart. Accordingly, the analog pre-processing circuit 828 isconfigured to pre-process the sensed signals from the accelerometer 826in a manner which conforms to the signal characteristics of both ofthese physical parameters. For example, if the frequencies of interestfor measuring the patient's level of activity are typically below 10 Hz,while the frequencies of interest for detecting heart sounds aretypically between 0.05 Hz and 50 Hz, then analog pre-processing circuit828 may include a low-pass filter having a cutoff frequency of 50 Hz.The controller 822 may then perform additional filtering in software, asdescribed above with reference to FIGS. 2-4, for example. Along withfiltering, analog pre-processing circuit 828 may perform otherprocessing functions including automatic gain control (AGC) functions.

The analog pre-processing circuit 828, analog-to-digital converter 830and controller 822 may operate together to acquire, measure, and isolateheart sounds, such as S1, S2, S3, and S4 heart sounds, as described in“METHOD AND APPARATUS FOR THIRD HEART SOUND DETECTION,” U.S. applicationSer. No. 10/746,853, filed Dec. 24, 2003, which is hereby incorporatedby reference for all it discloses. Alternatively, the analogpre-processing circuit 828 may simply provide automatic gain controlfunctionality.

In some embodiments, the controller 822 performs one or more of stepsthe depicted and described with reference to FIGS. 3, 5, 6, and 7.Instructions for performing the operations of the aforementioned Figuresmay be stored in the memory device 824, for example. Additionally, anyof the operations discussed and depicted with reference to FIGS. 3, 5,6, and 7 may be performed cooperatively by the controller 822 within theimplantable device 808 and another controller. For example, thecontroller 822 in the implantable device 808 may perform some of theoperations, communicate needed results (via communications link 806, forexample) to an external controller (contained in a programmer, forexample), which may perform the remaining operations, and which maycommunicate results to either another external device or to theimplantable device 802.

In another embodiment, the implantable device 808 has two pre-processingchannels for receiving sensed signals from accelerometer 826. In stillanother embodiment, implantable device 808 includes two accelerometers,with one accelerometer configured to generate sensed signalsrepresentative of the level of activity of the patient and the otheraccelerometer configured to generate sensed signals representative ofheart sounds. In these latter two embodiments, any hardware and/orsoftware processing performed on the sensed signals can conform to thespecific characteristics of the respective sensed signals. For example,the analog pre-processing circuit used for the level-of-activity sensedsignals can provide a low-pass filter with a cutoff frequency of 10 Hz,while the analog preprocessing circuit for the heart-sound sensedsignals can provide a band-pass filter with cutoff frequencies of 0.05and 50 Hz. In the latter case, each accelerometer can be selected,located and/or oriented to maximize the detection of the respectivephysical parameter. In yet another embodiment, if the implantable devicedoes not need to sense the level of activity of the patient, theaccelerometer 826 may measure only the sounds made by heart. In yetanother embodiment, an accelerometer for sensing heart sounds may belocated at the distal end of a lead. In such an embodiment, theimplantable device 802 may include an internal accelerometer (such asaccelerometer 826) for detection of the patient's motion-based activitylevel.

The implantable device 802 may include or communicate with a pressuresensor that may be adapted for placement in the pulmonary artery orright ventricle, for example. Data from the pressure sensor may berelayed to the controller 822 via an analog pre-processing circuit andanalog-to-digital converter, in a manner analogous to conveyance ofaccelerometer data, for example. Such data may be used to determine apreload patient's preload level, as discussed with reference to knownvariations of the method of FIG. 3, for example.

The controller 822 is capable of bi-directional communications with anexternal system 804 via an I/O interface 832. In one embodiment, the I/Ointerface 832 communicates using RF signals, which may be understood toinclude inductive coupling. In other embodiments, the I/O interface 832communicates using optical signals, or a combination of RF and opticalsignals (e.g., RF signals for receiving data from the external system804 and optical signals for transmitting data to external system 804, orvice-versa). The controller 822 uses the I/O interface 832 forbi-directional communications with the external system 804 to supportconventional monitoring, diagnostic and configuration pacemakerfunctions. The controller 822 may also use the I/O interface 832 totelemeter data representative of the heart sounds sensed byaccelerometer 826 to the external system 804. In various embodiments,the controller 822 further uses the I/O interface 832 to telemeter datarepresentative of cardiac electrical signals (i.e., electrogram or EGMsignals), which may include data representative of atrial electricalsignals, sensed by the atrial sensing electrode, and/or datarepresentative of ventricular electrical signals, sensed by theventricular sensing electrode. Thus, implantable system 802 is capableof sensing heart sounds, atrial electrical signals and ventricularelectrical signals, and of telemetering data representative of the heartsounds and/or cardiac electrical signals to external system 804. Inother embodiments, the controller 822 telemeters data representative ofcardiac electrical signals which were sensed by other configurations ofinternal cardiac sensing electrodes.

The external system 804 may include an external device 842. The externaldevice 842 may include an external controller 846, an I/O interface 848,user input device(s) 850, and user output device(s) 852. Using the I/Ointerface 848, the external controller 846 is configured forbi-directional communications with the implantable device 808, forreceiving input signals from input device(s) 850, and for applyingcontrol signals to output device(s) 852. The input device(s) 850 includeat least one input device which allows a user (e.g., a physician, nurse,medical technician, etc.) to generate input signals to control theoperation of external device 842, such as at least one user-actuatableswitch, knob, keyboard, pointing device (e.g., mouse), touch-screen,voice-recognition circuit, etc. The output device(s) 852 include atleast one display device (e.g., CRT, flat-panel display, etc.), audiodevice (e.g., speaker, headphone), or other output device whichgenerates user-perceivable outputs (e.g., visual displays, sounds, etc.)in response to control signals. The external controller 846 may beconfigured to receive the data representative of heart sounds, atrialelectrical signals and/or ventricular electrical signals fromimplantable system 802, and to generate control signals that, whenapplied to output device(s) 852, cause the output device(s) to generateoutputs that are representative of the heart sounds, the atrialelectrical signals and/or the ventricular electrical signals.

In one embodiment, the system 800 further includes a remote system 854operatively coupled to communicate with the external system 804 viatransmission media 856. The remote system 854 includes one or more userinput device(s) 858, and one or more user output device(s) 860, whichallow a remote user to interact with remote system 854. The transmissionmedia 856 includes, for example, a telephone line, electrical or opticalcable, RF interface, satellite link, local area network (LAN), wide areanetwork (WAN) such as the Internet, etc. The remote system 854cooperates with external system 804 to allow a user located at a remotelocation to perform any of the diagnostic or monitoring functions thatmay be performed by a user located at external system 804. For example,data representative of heart sounds and/or cardiac electrical signalsare communicated by the external system 804 to the remote system 854 viathe transmission media 856 to provide a visual display and/or an audiooutput on the output device(s) 860, thereby allowing a physician at theremote location to aid in the diagnosis of a patient. In variousexamples, the system 854 may be located in another room, another floor,another building, another city or other geographic entity, across a bodyof water, at another altitude, etc., from the external system 804.

The I/O interface 832 may establish a communication link with acommunication device in physical proximity to the patient. For example,the I/O interface may establish a data link with a personal digitalassistant, and may upload or download any of the data mentionedpreviously or hereafter. The personal digital assistant may, in turn,establish a link with an access point, so that the link may beeffectively extended over a network, such as the Internet.

Embodiments of the invention may be implemented in one or a combinationof hardware, firmware, and software. Embodiments of the invention mayalso be implemented as instructions stored on a machine-readable medium,which may be read and executed by at least one processor to perform theoperations described herein. A machine-readable medium may include anymechanism for storing or transmitting information in a form readable bya machine (e.g., a computer). For example, a machine-readable medium mayinclude read-only memory (ROM), random-access memory (RAM), magneticdisc storage media, optical storage media, flash-memory devices,electrical, optical, acoustical or other form of propagated signals(e.g., carrier waves, infrared signals, digital signals, etc.), andothers.

The Abstract is provided to comply with 37 C.F.R. Section 1.72(b)requiring an abstract that will allow the reader to ascertain the natureand gist of the technical disclosure. It is submitted with theunderstanding that it will not be used to limit or interpret the scopeor meaning of the claims.

In the foregoing detailed description, various features are occasionallygrouped together in a single embodiment for the purpose of streamliningthe disclosure. This method of disclosure is not to be interpreted asreflecting an intention that the claimed embodiments of the subjectmatter require more features than are expressly recited in each claim.Rather, as the following claims reflect, inventive subject matter liesin less than all features of a single disclosed embodiment. Thus, thefollowing claims are hereby incorporated into the detailed description,with each claim standing on its own as a separate embodiment.

1. A system comprising: an ambulatory device including: a transducer;and a control circuit coupled to the transducer, the control circuitconfigured to: monitor an S1 heart sound amplitude emitted by a heart ofa patient; monitor a proxy variable indicating preload exhibited by theheart, the proxy variable including at least one of a heart soundamplitude or a blood pressure magnitude; measure a first inotropic statedefined by a state variable pair obtained during a first time period,the state variable pair comprising: (1) an S1 heart sound amplitudevalue; and (2) a proxy variable value; measure a second inotropic statedefined by a state variable pair obtained during a second time period,the state variable pair comprising: (1) an S1 heart sound amplitudevalue; and (2) a proxy variable value; and determine whether the hearthas exhibited an inotropic state change by comparing the state variablepair of the second inotropic state to the state variable pair of thefirst inotropic state.
 2. The system of claim 1, wherein the controlcircuit is configured to communicate a control signal to a device orprocess using information about the determined inotropic state change.3. The system of claim 1 comprising a preload altering device, whereinthe control circuit is configured to communicate a control signal to thepreload altering device using information about the determined inotropicstate change.
 4. The system of claim 3, wherein the preload alteringdevice includes a substance dispenser configured to deliver a substanceto the patient.
 5. The system of claim 4, wherein the substance isconfigured to alter a fluid status of the patient.
 6. The system ofclaim 1 comprising an inotropic state altering device, wherein thecontrol circuit is configured to communicate a control signal to theinotropic state altering device using information about the determinedinotropic state change.
 7. The system of claim 1, wherein the controlcircuit monitors a proxy variable indicating preload by monitoring an S3heart sound.
 8. The system of claim 1, wherein the control circuitmonitors a proxy variable indicating preload by monitoring an S4 heartsound.
 9. The system of claim 1, wherein the control circuit monitors aproxy variable indicating preload by: sensing a plurality of S3 or S4heart sounds emitted by a heart of a patient, each of which isrepresented as a time-varying signal with at least one maxima andminima; and finding a greatest difference between a minima and maximathat are consecutive for each of the time-varying signals representingthe plurality of S3 or S4 heart sounds, yielding a set of peak-to-peakdifferences; and wherein the control circuit monitors an inotropic stateof the heart, using the set of peak-to-peak differences and an indicatorof stroke volume.
 10. The system of claim 1, wherein the ambulatorydevice includes a pressure sensor in data communication with the controlcircuit, and wherein the control circuit monitors a proxy variableindicating preload by monitoring blood pressure.
 11. The system of claim10, wherein the pressure sensor is configured to be located in a rightventricle.
 12. The system of claim 10, wherein the pressure sensor isconfigured to be located in a pulmonary artery.
 13. The system of claim1, wherein the control circuit is configured to determine that the hearthas exhibited an inotropic state change by identifying an occurrence inwhich the S1 heart sound indicates a change in stroke volume and theproxy variable indicates a change in preload.
 14. The system of claim13, wherein the S1 heart sound indicates an elevation in stroke volumeand the proxy variable indicates a decline in preload.
 15. The system ofclaim 13, wherein the S1 heart sound indicates a decline in strokevolume and the proxy variable indicates an elevation in preload.
 16. Thesystem of claim 1, wherein the ambulatory device comprises: stimulationand sensing circuitry interposed between the control circuit and anelectrode system configured to make electrical contact with the heart;and wherein the control circuit is configured to apply cardiacresynchronization therapy to the heart, based upon a set of parameters.17. The system of claim 16, wherein the control circuit is configured toadjust one or more of the set of parameters based upon the inotropicstate or preload level exhibited by the heart.
 18. The system of claim1, wherein: the ambulatory device comprises an activity sensor coupledto the control circuit, the activity sensor generating a signalexhibiting an time-varying characteristic indicating an activity levelof the patient; and the control circuit is configured to determineventricular function, based upon the S1 heart sound, the proxy variable,and the signal generated by the activity sensor.
 19. A systemcomprising: a preload altering device; and an ambulatory deviceincluding: a transducer; and a control circuit coupled to thetransducer, the control circuit configured to: monitor an S1 heart soundamplitude emitted by a heart of a patient; monitor a proxy variableindicating preload exhibited by the heart, the proxy variable includingat least one of a heart sound amplitude or a blood pressure magnitude;measure a first inotropic state defined by a state variable pairobtained during a first time period, the state variable pair comprising:(1) an S1 heart sound amplitude value; and (2) a proxy variable value;measure a second inotropic state defined by a state variable pairobtained during a second time period, the state variable paircomprising: (1) an S1 heart sound amplitude value; and (2) a proxyvariable value; and determine whether the heart has exhibited aninotropic state change by comparing the state variable pair of thesecond inotropic state to the state variable pair of the first inotropicstate; and communicate a control signal to the preload altering deviceusing information about the determined inotropic state change; whereinthe control circuit monitors a proxy variable indicating preload bymonitoring an S3 or S4 heart sound or a blood pressure; and wherein thecontrol circuit monitors a proxy variable indicating preload by: sensinga plurality of S3 or S4 heart sounds emitted by a heart of a patient,each of which is represented as a time-varying signal with at least onemaxima and minima; and finding a greatest difference between a minimaand maxima that are consecutive for each of the time-varying signalsrepresenting the plurality of S3 or S4 heart sounds, yielding a set ofpeak-to-peak differences; and wherein the control circuit monitors aninotropic state of the heart, using the set of peak-to-peak differencesand an indicator of stroke volume.
 20. A system comprising: an inotropicstate altering device; and an ambulatory device including: a transducer;and a control circuit coupled to the transducer, the control circuitconfigured to: monitor an S1 heart sound amplitude emitted by a heart ofa patient; monitor a proxy variable indicating preload exhibited by theheart, the proxy variable including at least one of a heart soundamplitude or a blood pressure magnitude; measure a first inotropic statedefined by a state variable pair obtained during a first time period,the state variable pair comprising: (1) an S1 heart sound amplitudevalue; and (2) a proxy variable value; measure a second inotropic statedefined by a state variable pair obtained during a second time period,the state variable pair comprising: (1) an S1 heart sound amplitudevalue; and (2) a proxy variable value; and determine whether the hearthas exhibited an inotropic state change by comparing the state variablepair of the second inotropic state to the state variable pair of thefirst inotropic state; and communicate a control signal to the inotropicstate altering device using information about the determined inotropicstate change; wherein the control circuit monitors a proxy variableindicating preload by monitoring an S3 or S4 heart sound or bloodpressure; and wherein the control circuit monitors a proxy variableindicating preload by: sensing a plurality of S3 or S4 heart soundsemitted by a heart of a patient, each of which is represented as atime-varying signal with at least one maxima and minima; and finding agreatest difference between a minima and maxima that are consecutive foreach of the time-varying signals representing the plurality of S3 or S4heart sounds, yielding a set of peak-to-peak differences; and whereinthe control circuit monitors an inotropic state of the heart, using theset of peak-to-peak differences and an indicator of stroke volume.